JP2001269317A - Ophthalmic device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ophthalmic device that can position plural pieces of measured data measured at different timing and can thus easily and precisely compare and analyze the pieces of measured data among other operations. SOLUTION: The ophthalmic device comprises a first input means for inputting first measured data obtained by a first measuring means for measuring an examined eye two-dimensionally, a second input means for inputting second measured data obtained by a second measuring means for measuring the examined eye two-dimensionally, and a data positioning means for positioning the first and second measured data in accordance with the first measuring means and with pickup images including a front eye region obtained at times of measurement by the first measuring means.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ophthalmologic apparatus used in an ophthalmic clinic, an optician, and the like.

[0002]

2. Description of the Related Art As an ophthalmologic apparatus, there is known a corneal shape measuring apparatus which projects a placido ring onto a cornea, measures a distribution of curvature over a wide range of the cornea from a reflected image thereof, and visualizes the distribution as a topography. I have. In addition, Japanese Patent Application Laid-Open
Japanese Patent Publication No. 108837 proposes a device for obtaining refractive power distributions at a large number of sites on the cornea, and furthermore, it is proposed to calculate a corneal ablation amount to be used in refractive surgery from both measurement data. .

[0003]

However, when obtaining new data from the measurement data measured at different timings as described above or examining the relationship between the measurement data, the two-dimensional positional relationship between the measurement data is considered. If they do not correspond, it is difficult to obtain accurate results, and comparison is not easy.

An object of the present invention is to provide an ophthalmologic apparatus which enables alignment of a plurality of measurement data measured at different timings, and which can easily and accurately compare and analyze each measurement data. Is a technical issue.

[0005]

Means for Solving the Problems In order to solve the above problems, the present invention is characterized by having the following configuration.

(1) The first method for measuring the eye to be examined two-dimensionally
A first input of the first measurement data obtained by the measuring means;
Input means, second input means for inputting second measurement data obtained by the second measurement means for two-dimensionally measuring the eye to be examined, and input means for obtaining the first measurement means and the first measurement means at each measurement. Data alignment means for aligning the first measurement data and the second measurement data based on the captured image including the anterior segment.

(2) The ophthalmologic apparatus according to (1), further comprising: arithmetic means for calculating new data from the aligned first and second measurement data; and display means for graphically displaying the calculation result or the calculation result. And an output unit for outputting to the external device.

(3) The ophthalmologic apparatus according to claim 1, further comprising display means for graphically displaying the aligned first and second measurement data under a common display standard.

(4) In the ophthalmologic apparatus of (1), the data positioning means performs positioning based on a common singular point of an anterior ocular segment image taken at the time of measurement.

(5) In the ophthalmologic apparatus of (1), at least one of the first measuring means and the second measuring means includes an index forming means for alignment, and the data positioning means includes an index image for alignment. , Based on the position detection.

(6) In the ophthalmologic apparatus according to (1), the first measuring means or the second measuring means further includes an index forming means for alignment, and the data positioning means includes a common singularity of an anterior ocular segment image. It is characterized by comprising a designation means for designating a point.

(7) In the ophthalmologic apparatus according to (1), the measurement means includes a first measurement optical system for obtaining the first measurement data, and a first measurement optical system for obtaining the second measurement data. It is characterized by having a different second measurement optical system.

(8) In the ophthalmologic apparatus of (1), the first measuring means includes a light projecting optical system for projecting a light beam for measuring a corneal curvature distribution and a light receiving optical system for receiving a measuring beam reflected from the cornea. A corneal shape measuring optical system having a corneal shape measuring optical system, wherein the second measuring means has an optical system for projecting a measuring light beam for measuring a refractive power distribution to the fundus and a light receiving optical system for receiving a reflected light beam from the fundus. It is an optical system.

(9) First for Two-Dimensional Measurement of the Eye to be Examined
A first input unit for inputting first measurement data obtained by the measurement unit and an alignment deviation at the time of measurement;
A second input unit for inputting second measurement data obtained by the second measurement means for dimensionally measuring and the misalignment at the time of measurement;
Input means for detecting a rotational displacement based on a captured image including the anterior segment obtained at each measurement of the first measuring means and the first measuring means, and detecting the position of the first measurement data and the second measurement data; Data alignment means for alignment.

[0015]

Embodiments of the present invention will be described below with reference to the drawings. FIG. 1 is a schematic external view of an ophthalmologic apparatus according to the present invention. FIG. 1A is a front view of the subject, and FIG. 1B is a side view.

Reference numeral 1 denotes a fixed base, on which a head support 2 for fixing the head of the subject is fixed. Reference numeral 5 denotes a measurement unit in which a measurement optical system, an alignment optical system, and the like are housed, and a measurement window 5a through which a measurement light beam or the like passes is provided substantially at the center of the measurement unit 5 on the side facing the subject. . The main unit 3 on which the measuring unit 5 is mounted moves on the fixed base 1 forward, backward, left and right (Z and X directions) by tilting the joystick 4 back and forth and left and right. By rotating a rotary knob 4 a provided on the joystick 4, a Y (vertical) driving device including a motor or the like operates, and the measuring unit 5 moves up and down (Y direction) with respect to the main body 3. I do.

Reference numeral 39 denotes a color monitor which displays information on the eye to be examined for observation, alignment information, measurement results, etc., to the examiner.

FIG. 2 is a view showing an optical system housed in the measuring section 5. Reference numeral 101 denotes an optical system that emits a light beam for measuring a corneal shape. Reference numeral 102 denotes a substantially hemispherical placid plate having an opening at the center, and a ring pattern having a large number of concentric light-transmitting portions and light-shielding portions centered on the optical axis L1 is formed. Reference numeral 103 denotes an illumination light source such as an LED. Light emitted from the light source 103 is reflected by a reflection plate 104 so as to illuminate the platinum plate 102 almost uniformly from behind. A ring pattern image is projected on the cornea of the subject's eye. Placid plate 10
An anterior ocular segment illumination light source 105 that emits near-infrared light is provided on the outer periphery of 2.

Behind the reflector 104, a target projection optical system 1 for detecting a working distance, comprising a light source 111 and a lens 112.
10, an index detection optical system 115 including a lens 116 and a position detection element 117 is provided. The light from the light source 111 is converted into a substantially parallel light beam by the lens 112,
Irradiation is performed on the patient's eye cornea from an oblique direction through an opening provided in the substrate 04 and the placid plate 102, and an index image of the light source 111 is projected on the cornea. The luminous flux of the index image formed on the cornea passes through openings provided in the placido plate 102 and the reflection plate 104 and enters the position detection element 117 via the lens 116 of the index detection optical system 115. From the position of the index image incident on the position detecting element 117, the alignment state of the working distance of the subject's eye with respect to the apparatus is detected.

Behind the optical axis L1, an eye refractive power measuring optical system 1 is provided.
20 are provided. The eye refractive power measuring optical system 120 is
Slit projection optical system 121 and slit image receiving optical system 13
1 Light source 1 of slit projection optical system 121
The near-infrared light beam emitted from 22 illuminates a slit opening provided in the rotating sector 123. The slit light beam scanned by the rotation of the rotating sector 123 is projected onto the projection lens 12.
4. After passing through the limiting aperture 125, the beam splitter 126
Is reflected by Thereafter, the light passes through a beam splitter 25 that makes the optical axes of the fixation optical system and the observation optical system coaxial, and is condensed in the vicinity of the cornea of the eye E, and then emitted to the fundus.

The slit image receiving optical system 131 has an optical axis L1.
A light-receiving lens 132 provided above, a mirror 133, a stop 134 provided on the optical axis L2 reflected by the mirror 133, and a light-receiving unit 135 are provided. The diaphragm 134 is disposed at the rear focal position of the light receiving lens 132. Light receiving unit 135
Are eight light receiving elements 136a to 136a located on the light receiving surface thereof at positions substantially conjugate with the cornea of the eye to be examined with respect to the light receiving lens 132.
36h. Among them, the light receiving elements 136a to 136a
6f is located on a straight line passing through the center of the light receiving surface (optical axis L2) so that the light receiving elements 136a and 136b, the light receiving elements 136c and 136d, and the light receiving elements 136e and 136f are respectively symmetrical with respect to the center of the light receiving surface. Is provided. The arrangement distances of the three pairs of light receiving elements are set so that the refractive power corresponding to each position in the meridian direction of the cornea can be detected (shown as the equivalent size on the cornea in FIG. 4). . On the other hand, the light receiving elements 136g and 136h
The light receiving elements 136a to 136f are provided symmetrically on a straight line orthogonal to the light receiving elements 136a to 136f about the optical axis L2.

In the eye-refractive-power measuring optical system 120, the rotating sector 123 and the light receiving section 135 are rotated around the optical axis in synchronization with each other by a rotating mechanism including a motor and gears.

Half mirrors 26, 27, 27 are placed on an optical axis L3 coaxial with the optical axis L1 by the beam splitter 25.
A lens 28, a fixation target 29, and a visible illumination light source 30 are arranged. The fixation target 29 has a fixation point in the center, and the surrounding area is configured to transmit visible light. Also, the lens 28
Is movable in the direction of the optical axis L3, changes the position of the fixation target 29 to fixate on the subject's eye, and applies fogging or adjustment load to the subject's eye when measuring the eye refractive power.

A lens 33 and an alignment light source 34 are arranged on an optical axis L4 coaxial with the optical axis L3 by the half mirror 27. When the light source 34 is turned on, an alignment for the up, down, left and right directions on the cornea of the eye to be examined is performed. An index light beam is emitted.

A lens 35 and a CCD camera 38 as an image pickup device are arranged on an optical axis L5 coaxial with the optical axis L3 by the half mirror 26. The CCD camera 38 reflects reflected light from the eye to be examined. Is received. CCD camera 3
The output from 8 is input to the monitor 39, and the captured image is displayed. The CCD camera 38 is used not only for observing the anterior segment but also for detecting the alignment index image, and is also used for detecting the placido ring image, and constitutes a part of the alignment optical system and the corneal shape measuring optical system.

Next, the operation of the apparatus will be described with reference to the block diagram of the control system shown in FIG. This apparatus has a function of performing a corneal shape measurement and an eye refractive power measurement, and analyzing the corneal ablation amount for refractive surgery based on both measurement data. In addition, the eye refractive power distribution in which the accommodation power of the eye has been released (eye refractive power distribution in far vision) and the eye refractive power distribution when accommodation is added to the eye (eye refractive power distribution in near vision) And has a function of analyzing the accommodation power of the lens.

(A) Analysis of corneal ablation amount First, measurement of the corneal shape will be described. In the measurement, the corneal shape measurement mode is selected by the mode changeover switch 40. The examiner performs the XYZ movement of the measurement unit 5 by operating the joystick 4 or the like while observing the anterior eye image of the subject's eye illuminated by the light source 105 on the monitor 39. The alignment in the XY directions is performed by the light source 34.
The target image formed at the optical center determined by the corneal optical system (hereinafter, referred to as the corneal center, which can also be treated as the visual axis center) is displayed on the monitor 39 with the aiming marker 60 (FIG. 5). (See Reference). The aiming marker 60 on the monitor 39 can be formed electrically, and is adjusted in advance so that the center of the aiming marker 60 and the imaging optical axis (measurement optical axis) of the CCD camera 38 coincide with each other. In the Z direction alignment, an indicator for alignment is displayed on the monitor 39 under the control of the control unit 50 based on the deviation information in the working distance direction obtained by the position detecting element 117. Therefore, the main body 3 is moved in the Z direction for adjustment.

After the alignment is completed, when the measurement switch 41 is pressed, the illumination light source 103 is turned on for a predetermined time, the placido ring is projected on the cornea of the eye to be examined, and the image of the anterior eye taken by the CCD camera 38 is displayed as an image. Memory 43
Is stored. The corneal shape calculation unit 53 performs image processing on the image stored in the image memory 43 to detect the edge of the placido ring image. Then, a corneal curvature distribution is obtained by obtaining each edge position with respect to the corneal center at every predetermined angle (1 degree) step.

Further, an alignment state calculating section 51 for determining an alignment state measures the apparatus based on an alignment index image (corneal bright spot by the light source 34) detected by the CCD camera 38 when the measurement switch 41 is pressed. The deviation information of the alignment in the XY directions with respect to the optical axis L1 is obtained. The deviation information of the alignment is stored in the storage unit 45 such as a hard disk together with the anterior segment image on which the Placido rings are projected and the distribution data of the corneal curvature. In addition, regarding the deviation information of the alignment at the time of measuring the corneal shape, the center of the inner Placido ring image can be detected as the corneal center position.

In order to measure the eye refractive power, the mode changeover switch 40 is set to a refractive power measuring mode. In the measurement of the refractive power of the eye, a measurement light beam is made to enter the eye, and the fundus reflection light passing through the pupil is received. here,
Generally, the center of the cornea and the center of the pupil substantially coincide with each other, but there are some eyes to be examined in which the center of the pupil is largely eccentric. In such a case, in the alignment in the XY directions based on the center of the cornea, the measurement light beam is eclipsed by the iris, and the reflected light beam required for measurement is not received, so that a measurement error is likely to occur.

The examiner observes the anterior eye image displayed on the monitor 39, and if the pupil is decentered from the center of the cornea, adjusts the alignment in the X and Y directions with reference to the center of the pupil. That is, as shown in FIG. 5, the alignment adjustment in the XY directions is performed so that the center of the pupil of the subject's eye is located at the center of the aiming marker 60 on the monitor 39. The Z direction is adjusted in advance by an indicator displayed on the monitor 39.

After the alignment is adjusted, the examiner presses the measurement switch 41. When the measurement switch 41 is pressed,
The anterior eye image captured by the CCD camera 38 is stored in the image memory 4.
3 and the eye-refractive-power measurement by the eye-refractive-power measuring optical system 120 is executed. The eye refractive power calculation unit 52
An eye refractive power distribution is obtained based on the phase difference between the output signals from the respective light receiving elements of the light receiving unit 135. First, a preliminary measurement is performed in the same manner as the refractive power of the conventional phase difference method, and based on the result, the lens 28 is moved to fog the eye to be inspected. Thereafter, based on the output signals of the light receiving elements 136g and 136h that change with the movement of the slit image on the light receiving section 135, the light receiving element 1
The corneal center (or visual axis center) in the meridian direction where 36a to 136f are located is determined. Next, based on the phase difference between the output signals of the light receiving elements 136a to 136f with respect to the center, the refractive power at the cornea corresponding to each light receiving element is determined. Rotating sector 123 of slit projection optical system 121 and light receiving section 1
35 around the optical axis in predetermined angle (1 degree) steps.
By calculating the refractive power for each meridian at each angle step while rotating the lens by degrees, the distribution of eye refractive power that changes in the meridian direction is obtained. The measurement of the refractive power distribution is basically the same as that of Japanese Patent Application Laid-Open No. 10-108837 by the present applicant.

When the measurement switch 41 is depressed, the alignment state calculation unit 51 determines the XY direction with respect to the optical axis L1 of the apparatus based on the alignment index image detected by the CCD camera 38, as in the case of the corneal shape measurement. Alignment deviation information is obtained. The alignment deviation information is stored in the storage unit 45 together with the measurement result of the eye refractive power distribution.

When the measurement data of the corneal curvature distribution and the measurement data of the eye refractive power distribution in the same eye to be examined are obtained as described above, the keyboard 58 connected to the control unit 50 is operated in accordance with the instruction displayed on the monitor 39. By operating the mouse 57, the measurement data and the deviation information of the alignment are transferred to the ablation amount analysis unit 54 and the monitor display control unit 5.
6, the map display of each measurement data and the calculation result of the corneal ablation amount are displayed on the monitor 39.

The map display of each measurement data will be described. In the above-described measurement of the eye refractive power distribution, as shown in FIG. 5, taking the case where the center of the pupil and the center of the cornea are eccentric as an example, alignment is performed so that the center of the pupil is located at the center of the aiming marker 60. Therefore, the alignment index image 62 formed at the center of the cornea is shifted from the center 61 of the measurement optical axis. On the other hand, at the time of measuring the corneal shape, the alignment index image 62 was aligned and measured so as to be at the center of the aiming marker 60, so that the center 61 of the measurement optical axis and the alignment index image 62 almost coincided with each other.

FIG. 6 shows a conventional color map display, in which a map 64a of the eye refractive power distribution is displayed on the left side of the same screen on the monitor 39, and a map 64 of the corneal curvature distribution is displayed on the right side.
b are displayed side by side. In the conventional format, in both cases, the center of the measurement optical axis at the time of measurement coincides with the cross marks 66a and 66b indicating the display center of each area. The black points 67a and 67b in the figure indicate the corneal center position, respectively, and are shown for convenience of explanation. When such a display is used to compare the relationship between the eye refractive power distribution map 64a and the corneal curvature distribution map 64b, it is difficult to understand the correspondence between the two-dimensional positional relationships at the corneal site.

Therefore, in the color map display for each measurement data according to the present embodiment, as shown in FIG. 7, the corneal center position obtained from the detection of the alignment index image 62 is determined by the cross marks 66a and 66b which are the centers of the respective map displays. , So that graphics are displayed under common display criteria,
The display on the monitor 39 is controlled by the monitor display control unit 56. That is, in the eye refractive power distribution map 64a, the map data is offset by the alignment deviation so that the corneal center is located at the center of the cross mark 66a.

With such a display, two of the measured data can be displayed.
It is easy to compare the positional relationship of the dimensional distribution, and it is easy to see. Note that reference numerals 65a and 64b in FIGS. 6 and 7 denote color bars indicating the color classification of each map display.

Further, by aligning both measurement data, both measurement data at the same position on the cornea can be easily associated with each other. For example, as shown in FIG. 8, when an arbitrary point 68 on the map display 64a or 64b is clicked with the mouse 57, the measured values at that point are displayed simultaneously. That is, map 6 of the eye refractive power distribution
4a displays the refractive power at that point, and the corneal curvature distribution map 64b simultaneously displays the corneal curvature at that point or the corneal refractive power converted from the corneal curvature. Even in such a display, if the positional relationship between the two is not maintained as shown in FIG. 6, the measured values at the same point will not be represented if they are misaligned.

The ablation amount analysis unit 54 obtains an ablation amount (corneal ablation amount) for refractive surgery by making the corneal center positions of the eye refractive power distribution data and the corneal curvature distribution data coincide two-dimensionally. . Hereinafter, the outline will be described.

First, the three-dimensional shape of the cornea is determined from the measured corneal curvature, and converted into corneal refractive power using Snell's law. Next, the measured eye refractive power distribution data is converted into eye refractive power distribution data at the cornea position. By these,
A value representing the refractive power required to make the eye to be examined emmetropic in the form of corneal refractive power is determined. In the present specification, this is referred to as “equivalent emmetropic corneal refractive power”, and equivalent emmetropic corneal refractive power = corneal refractive power +
It is calculated by eye refractive power. Then, the distribution data of the equivalent emmetropic corneal refractive power is converted into the distribution data of the corneal curvature, that is, the three-dimensional shape data of the cornea, using Snell's law. Finally, the ablation amount is calculated by subtracting the three-dimensional shape data obtained from the corneal curvature distribution obtained by converting the equivalent corneal refractive power from the three-dimensional shape obtained from the corneal curvature obtained by the corneal shape measurement. The calculated distribution data of the equivalent emmetropia corneal refractive power is also graphically displayed in a color map as shown in FIG. 7, and the ablation amount is graphically displayed in a three-dimensional shape such as a bird's eye view.

The data of the obtained ablation amount is as follows:
Communication port 59b and floppy disk drive 59a
It is output to the corneal surgery device 90 side via the floppy disk inserted in the device and used for corneal surgery.

From the corneal shape measurement data and the eye refractive power distribution measurement data measured at different timings as described above, when calculating the equivalent data of the equivalent corneal refractive power and the amount of ablation, which are new data, the two-dimensional data of both measurement data are used. Accurate results are obtained by aligning the target positions.

In the above description, the displacement in the X and Y directions is corrected based on the position of the alignment index image. However, the center of the pupil is obtained from the captured image of the anterior segment obtained at each measurement, and this is used for two-dimensional registration of both measurement data. It may be a reference position. In order to obtain the pupil center, for example, by image processing of a captured image, the pupil is cut by a vertical line and a horizontal line, and the intersection of each vertical bisector of a line connecting the intersection with the edge of the pupil is set as the pupil center. . Alternatively, the contour edge of the pupil may be obtained by image processing, and the center of gravity of the inner area may be set as the pupil center.

In the above description, an example has been described in which the measurement data is aligned so as to correct the deviation in the X and Y directions. However, when there is a misalignment of the rotation angle (tilt angle) of the eye in both measurements, this rotation is performed. It is preferable that the position is corrected by correcting the angle. An example of a method for aligning the rotational displacement of the eye is as follows.

FIG. 9 is an example of a screen in which an anterior segment image 70 photographed at the time of measuring the eye refractive power distribution and an anterior segment image 75 photographed at the time of measuring the corneal shape are simultaneously displayed on the monitor 39. Each anterior segment image is stored in the image memory 43 at the time of measurement. Note that in this example, it is assumed that alignment in the XY directions is performed at the center of the cornea in both measurements, and that the eye (head) is tilted when measuring the refractive power distribution of the eye with respect to the measurement of the corneal shape. I do.

The examiner observes the anterior eye images 70 and 75, finds a singular point common to both from the iris pattern, and
The two singular points 71 and 72 at 0 are clicked with the mouse 57, and a line segment 73 connecting the singular points 71 and 72 is drawn. Also in the anterior segment image 75 on which the placido ring image is reflected, two singular points 76 and 77 that coincide with the left anterior segment image 70 are clicked with the mouse 57 and a line segment 78 connecting the singular points 76 and 77.
pull. The alignment deviation of the rotation angle of the eye in both the measurements can be determined from the two line segments 73 and 78, and the alignment state calculation unit 51 that determines the alignment state obtains the amount of deviation of the rotation angle. Then, as shown in FIGS. 7 and 8 described above, the map 64a of the eye refractive power distribution,
When displaying the corneal curvature distribution map 64b, the monitor display control unit 56 controls the display of the monitor 39 so as to correct the positional difference between the two maps by correcting the deviation of the rotation angle.

In calculating the equivalent emmetropic corneal refractive power and the ablation amount, the ablation amount analyzing unit 54 corrects the deviation of the rotation angle and matches the positional relationship between the eye refractive power distribution data and the corneal curvature distribution data. Perform the operation.

In this embodiment, the singular point is an iris pattern. However, the singular point may be a point determined from the position of the eyelashes, the shadow of the nose, and the like. It is also possible for the apparatus to automatically extract a singular point by image analysis.

(B) Analysis of accommodation power of lens Next, measurement of eye refractive power distribution in far vision and measurement of eye refractive power distribution in near vision are performed, and the accommodation power of the lens is determined from both measurement data. The case of analysis will be described.

The mode changeover switch 40 is pressed to set the far / near eye refractive power distribution measurement mode. First, the eye refractive power distribution measurement in far vision is performed using the eye refractive power measurement optical system 120 in the same manner as the measurement of the corneal ablation amount calculation. In this case, since the measurement is performed by the fogging method, this data is the eye refractive power distribution from which the accommodation of the eye has been canceled. The alignment state at the time of measurement is obtained based on the detection of the alignment index image 62 in the same manner as described above, and alignment deviation information is obtained by the alignment state calculation unit 51 and stored in the storage unit 45 together with the measurement result.

Next, the lens 2 of the fixation optical system in FIG.
By moving the position 8 under the control of the control unit 50, the image position of the fixation target 29 is brought into the near vision state of a predetermined distance,
An eye refractive power distribution when an accommodation load is applied to the eye is measured. For example, if the SE value (equivalent spherical value) of the refractive power of the far eye measured earlier is -3D, the image of the fixation target 29 is -3D-2.5D = The lens 28 is moved so as to be located at -5.5D.

When an accommodation load is applied, the pupil tends to constrict the pupil, so that the alignment may not be performed at the center of the cornea in some cases. In the measurement of the eye refractive power distribution in near vision, it is assumed that alignment is performed at the center of the pupil as in the above example. The deviation information of the alignment at this time is obtained by the alignment state calculation unit 51, and is stored in the storage unit 45 together with the measurement result.

When the measurement results of the eye refractive power distribution for far vision and near vision are obtained, the accommodation power analysis unit 55 calculates the refractive power distribution data for far vision and the eye refractive power distribution data for near vision. ,
The refractive power distribution of the difference is calculated. The eye focuses on distant and near objects by changing the thickness of the lens, so the refractive power change of the lens can be obtained from the difference in eye refractive power distribution between far vision and near vision, and accommodation It can be used for power evaluation and diagnosis. At this time, the adjusting force analysis unit 55
By calculating the positional relationship between the two pieces of refractive power distribution data based on the alignment deviation information, accurate data can be obtained by removing the effect of two-dimensional displacement. Further, when the rotation of the eye is different between the two measurements, the deviation of the rotation angle is corrected in the same manner as described above.

Further, the eye refractive power distribution in far vision, the eye refractive power distribution in near vision, and the eye refractive power distribution of the difference are displayed on the same screen of the monitor 39 in a color map as in the previous example. Displayed side by side. Also in this case, the display center position of each map is displayed so as to match the corneal center as the alignment reference, and the display is corrected for the rotation angle, so that the comparison of the state of the eye refractive power distribution in each map is accurate. Can be done.

In the measurement of the refractive power distribution of the eye in the above embodiment, an example in which alignment is performed at the center of the pupil has been described. However, even when alignment is performed at the center of the cornea, the alignment usually includes some errors. By adjusting the two-dimensional position of each measurement data as described above, the subsequent analysis and the like can be performed more accurately.

In the above embodiment, the two measurement functions of the eye refractive power distribution measurement and the corneal shape measurement are included in one device, but they may be separate devices. In this case, the measurement data and alignment information from each measuring device are input to an external computer, and the external computer aligns the two measurement data to perform display and calculation.

Further, in addition to the eye refractive power distribution and the corneal curvature distribution described above, the measurement data of the corneal thickness distribution is one of the measurement data requiring two-dimensional alignment. The measurement of the corneal thickness distribution is performed as follows. Slit light is injected into the cornea from an oblique direction, and a slit cross-sectional image is continuously photographed from the front while moving the slit light, and a front corneal curve and a posterior corneal curve are detected from the image. Then, the corneal thickness at an arbitrary position of the cornea is determined from the anterior corneal curve and the posterior corneal curve, and the distribution of the corneal thickness is obtained by calculating over the entire area. Alternatively, the slit light is input from the front, and the slit light is rotated around the cornea, and the slit cross-sectional images are continuously photographed by a camera arranged obliquely based on the Scheimpflug principle, and the photographed image is analyzed. Thereby, a distribution of the corneal thickness can be obtained.

By comparing and analyzing the distribution of the corneal thickness and the two-dimensional data of the ablation amount described in the above embodiment, it is examined whether the ablation amount is suitable for the person's corneal thickness. It becomes possible. Also in this case, by comparing the two-dimensional position of each data based on the determination result of the alignment state at each measurement, the comparison and analysis of each data can be performed accurately.

[0060]

As described above, according to the present invention,
Two-dimensional alignment of data measured at different timings is possible, and comparison and analysis of each data can be performed accurately and easily.

[Brief description of the drawings]

FIG. 1 is a schematic external view of an ophthalmologic apparatus according to an embodiment.

FIG. 2 is a schematic layout diagram of an optical system arranged in a measurement unit.

FIG. 3 is a diagram showing a schematic configuration of a control system.

FIG. 4 is a diagram showing an arrangement of light receiving elements included in a light receiving unit of the eye refractive power measuring optical system.

FIG. 5 is a diagram showing an alignment screen for eye refractive power measurement.

FIG. 6 is a diagram showing an analysis screen for eye refractive power measurement and corneal curvature measurement.

FIG. 7 is a diagram showing an analysis screen in an eye refractive power measurement and a corneal curvature measurement using an alignment index image as a reference position.

FIG. 8 is a diagram showing a screen in which, when an arbitrary point is selected with an alignment index image as a reference position in the eye refractive power measurement and the corneal curvature measurement, respective data are simultaneously displayed.

FIG. 9 is a diagram illustrating a method of correcting angle shift measurement data.

[Explanation of symbols]

 5 Measurement unit 34 Alignment light source 38 CCD camera 39 Monitor 43 Image memory 45 Storage unit 50 Control unit 51 Alignment state calculation unit 52 Eye refractive power calculation unit 53 Corneal shape calculation unit 54 Ablation amount analysis unit 55 Adjusting force analysis unit 56 Monitor display Control unit 59a Floppy disk drive 59b Communication port 61 Center of measurement optical axis 62 Alignment index image 66a Cross mark 66b Cross mark 71, 72, 76, 77 Singular point 101 Optical system 121 for projecting light beam for corneal shape measurement 121 Slit projection Optical system 131 Slit image receiving optical system 135 Light receiving unit

Continued on the front page (51) Int.Cl. ⁷ Identification symbol FI Theme coat II (reference) G06T 1/00 290 A61B 3/10 MHW A61F 9/00 570

Claims (9)

[Claims] A first measuring means for inputting first measurement data obtained by a first measuring means for two-dimensionally measuring the eye to be inspected; and a second measuring means for two-dimensionally measuring the eye to be inspected. Second input means for inputting the obtained second measurement data, and the first measurement data and the first measurement data based on the captured image including the anterior segment obtained at each measurement of the first measurement means and the first measurement means. An ophthalmologic apparatus, comprising: data alignment means for aligning the second measurement data. 2. The ophthalmologic apparatus according to claim 1, further comprising: arithmetic means for calculating new data from the first and second measurement data which have been aligned; and display means for graphically displaying the calculation result or displaying the calculation result. An ophthalmologic apparatus comprising: output means for outputting to an external device. 3. The ophthalmologic apparatus according to claim 1, further comprising display means for graphically displaying said first and second measurement data, each of which is aligned, under a common display standard. 4. The ophthalmologic apparatus according to claim 1, wherein the data positioning unit performs positioning based on a common singular point of the anterior ocular segment image captured at the time of measurement. 5. The ophthalmologic apparatus according to claim 1, further comprising:
An ophthalmologic apparatus, wherein at least one of the measurement unit and the second measurement unit includes an alignment index forming unit, and the data alignment unit is based on position detection of an alignment index image. 6. The ophthalmologic apparatus according to claim 1, further comprising:
An ophthalmologic apparatus, wherein the measuring means or the second measuring means includes an index forming means for alignment, and the data positioning means includes a specifying means for specifying a common singular point of the anterior ocular segment image. 7. The ophthalmologic apparatus according to claim 1, wherein the measurement unit is different from the first measurement optical system for obtaining the first measurement data and the first measurement optical system for obtaining the second measurement data. An ophthalmologic apparatus comprising a second measurement optical system. 8. The ophthalmologic apparatus according to claim 1, wherein the first
The measuring means is a corneal shape measuring optical system having a light projecting optical system for projecting a light beam for measuring a corneal curvature distribution and a light receiving optical system for receiving a measuring light beam reflected from the cornea. An ophthalmologic apparatus comprising: an eye refractive power distribution measuring optical system having an optical system for projecting a measuring light beam for measuring a refractive power distribution and a light receiving optical system for receiving a reflected light beam from the fundus. 9. A first input means for inputting first measurement data obtained by a first measuring means for two-dimensionally measuring an eye to be inspected and an alignment deviation at the time of measurement, and two-dimensionally measuring the eye to be inspected. A second input unit for inputting second measurement data obtained by the second measurement unit and an alignment deviation at the time of measurement, and an anterior eye part obtained at each measurement of the first measurement unit and the first measurement unit. An ophthalmologic apparatus comprising: a data alignment unit configured to detect a rotational displacement based on a captured image including the alignment data and align the first measurement data and the second measurement data.